Classifications

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  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
  • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
• • A—HUMAN NECESSITIES
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  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
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  • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
• • G—PHYSICS
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  • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/1717—Systems in which incident light is modified in accordance with the properties of the material investigated with a modulation of one or more physical properties of the sample during the optical investigation, e.g. electro-reflectance
• • G—PHYSICS
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  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
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  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
  • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
  • G01N21/314—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths
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  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
  • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
  • G01N21/35—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light
  • G01N21/359—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry using infrared light using near infrared light
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/47—Scattering, i.e. diffuse reflection
  • G01N21/49—Scattering, i.e. diffuse reflection within a body or fluid
• • G—PHYSICS
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  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
  • G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
  • G01N33/483—Physical analysis of biological material
  • G01N33/487—Physical analysis of biological material of liquid biological material
  • G01N33/49—Blood
• • A—HUMAN NECESSITIES
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  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
  • A61B2560/04—Constructional details of apparatus
  • A61B2560/0431—Portable apparatus, e.g. comprising a handle or case
• • A—HUMAN NECESSITIES
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  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
  • A61B2562/0233—Special features of optical sensors or probes classified in A61B5/00
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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  • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
  • A61B2562/14—Coupling media or elements to improve sensor contact with skin or tissue
  • A61B2562/146—Coupling media or elements to improve sensor contact with skin or tissue for optical coupling
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/0048—Detecting, measuring or recording by applying mechanical forces or stimuli
  • A61B5/0051—Detecting, measuring or recording by applying mechanical forces or stimuli by applying vibrations
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
  • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
  • A61B5/6813—Specially adapted to be attached to a specific body part
  • A61B5/6814—Head
  • A61B5/6815—Ear
  • A61B5/6816—Ear lobe
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
  • A61B5/00—Measuring for diagnostic purposes; Identification of persons
  • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
  • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
  • A61B5/6813—Specially adapted to be attached to a specific body part
  • A61B5/6825—Hand
  • A61B5/6826—Finger
• • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
  • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
  • F04C—ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; ROTARY-PISTON, OR OSCILLATING-PISTON, POSITIVE-DISPLACEMENT PUMPS
  • F04C2270/00—Control; Monitoring or safety arrangements
  • F04C2270/04—Force
  • F04C2270/041—Controlled or regulated
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
  • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
  • G01N21/314—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths
  • G01N2021/3148—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths using three or more wavelengths
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/47—Scattering, i.e. diffuse reflection
  • G01N2021/4704—Angular selective
  • G01N2021/4709—Backscatter
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/47—Scattering, i.e. diffuse reflection
  • G01N21/4738—Diffuse reflection, e.g. also for testing fluids, fibrous materials
  • G01N21/474—Details of optical heads therefor, e.g. using optical fibres
  • G01N2021/4742—Details of optical heads therefor, e.g. using optical fibres comprising optical fibres
  • G01N2021/475—Bifurcated bundle
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
  • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
  • G01N21/47—Scattering, i.e. diffuse reflection
  • G01N21/4738—Diffuse reflection, e.g. also for testing fluids, fibrous materials
  • G01N21/474—Details of optical heads therefor, e.g. using optical fibres
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N2201/00—Features of devices classified in G01N21/00
  • G01N2201/02—Mechanical
  • G01N2201/022—Casings
  • G01N2201/0221—Portable; cableless; compact; hand-held
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N2201/00—Features of devices classified in G01N21/00
  • G01N2201/06—Illumination; Optics
  • G01N2201/063—Illuminating optical parts
  • G01N2201/0631—Homogeneising elements
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N2201/00—Features of devices classified in G01N21/00
  • G01N2201/06—Illumination; Optics
  • G01N2201/063—Illuminating optical parts
  • G01N2201/0636—Reflectors

Definitions

• the present disclosure generally relates to the field of biomedical testing. More specifically, the present disclosure relates to methods and apparatus for noninvasive measurement of concentration of analytes in body tissues.
• Noninvasive diagnosis and measurement of blood glucose concentration has attracted tremendous attention in the past two decades because of the emergence of diabetes as an epidemic, particularly when associated with an increased overall obesity of the population.
• Noninvasive measurement of glucose offers the potential for increased frequency of testing, and thus, enable tighter control of blood glucose concentrations through concomitant adjustment of insulin doses.
• Noninvasive detection techniques also offer the potential for a portable, closed-loop system for monitoring and regulating insulin dosage.
• the method utilizes two wavelengths- a principle wavelength which is highly absorbed in the target analyte, and a reference wavelength, selected using a balancing process, which is not (or much less) absorbed in the target analyte.
• the two wavelengths are selected to have substantially identical extinction coefficients in the background matrix.
• the Optical Bridge balancing process is used to vary the two alternating wavelengths and their relative intensities such that in the absence of analyte, the detector signal is essentially zero. That is, the Optical Bridge uses the two near infrared wavelengths to "null out” the background absorption so that the analyte concentration becomes much more visible.
• Harjunmaa et al. disclosed a method of changing the extracellular to intracellular fluid ratio of the tissue matrix by varying the mechanical pressure on the tissue, and zeroing the transmitted/reflected signal (balancing) when there is a minimum level of analyte present in the sample.
• Harjunmaa et al. disclosed continuous estimation of the amount of fluid containing the target analyte within the sample using another radiation (such as green light which is absorbed by hemoglobin), and combining the output of the sample detector with the fluid volume estimate to calculate the analyte concentration. Further, in U.S. Application No. 1/526,564, which is also incorporated herein by reference, Harjunmaa et al. disclosed a method of producing a radiation beam using three fixed-wavelength laser diodes instead of tuning the laser wavelengths during use.
• the present disclosure describes a method and apparatus for noninvasively measuring the concentration of a target analyte in a sample using a fiberless transflectance probe.
• a first aspect of the present disclosure is an illustrative apparatus for noninvasively interrogating a target region for measuring an amount of a target analyte, wherein the apparatus comprises a source for generating a combined beam of electromagnetic radiation including at least two repetitive periods of radiation having different wavelengths, at least two of the wavelengths having different absorption coefficients for the target analyte.
• the apparatus further comprises a detector arranged to detect a portion of the radiation backscattered by the target region, the detector generating an output signal proportional to the detected intensity of the combined beam at each of the two repetitive periods of radiation, and a fiberless transflectance probe for directing the beam of electromagnetic radiation to the target region and conducting the backscattered light to the detector, wherein the fiberless transflectance probe comprises a tapered tubular housing with an inner reflective surface, a cylindrical optical rod with an outer reflective surface and a detection window through which the radiation beam is transmitted to the target region.
• Another aspect of the present disclosure is an illustrative transflectance probe for measuring a property of a sample, which includes a detection window through which the sample is irradiated, an optical rod with an outer reflective surface positioned perpendicular to the detection window, a tapered tubular housing with an inner reflective surface positioned around the optical rod, at least one light source for irradiating the sample, and a detector positioned at the proximal end of the optical rod for detecting the light backscattered by the sample.
• Yet another aspect of the present disclosure is an illustrative method of noninvasive ⁇ interrogating a target region for measuring an amount of a target analyte, comprising the steps of providing a fiberless transflectance probe comprising a tapered tubular housing with an inner reflective surface, a detection window and an optical rod with an outer reflective surface positioned perpendicular to the optical rod.
• the method further includes providing at least two light sources operating at two different wavelengths for generating a radiation beam consisting of at least two time multiplexed components, transmitting the radiation beam to the target region by reflecting on the inner surface of the tubular housing and the outer surface of the optical rod, conducting the backscattered beam from the target region to the detector by reflecting on the inner surface of the optical rod, and providing a detector that detects the backscattered beam and produces an output signal indicative of the differential absorption of the two wavelengths by the target region.
• FIG. 1 is a schematic diagram of an analyte testing device, in accordance with an embodiment of the present disclosure
• FIGS. 2A and 2B illustrate the operation of the Optical Bridge, in accordance with an embodiment of the present disclosure
• FIG. 3A is a schematic diagram of an illustrative fiberless transflectance probe embodiment
• FIG. 3B is a schematic diagram of the distal end of the fiberless transflectance probe embodiment illustrated in FIG. 3A;
• FIG. 4 illustrates the distribution of the incident radiation beam on a measurement site, in accordance with an embodiment of the present disclosure.
• an optical system comprising a fiberless transflectance probe is used to measure the concentration of a target analyte in a fluid within a sample matrix.
• the analyte concentration is measured and analyzed using a portable device developed using Optical BridgeTM technology.
• noninvasive optical measurements of the analyte concentration are performed using a beam of electromagnetic radiation which alternates at a particular frequency between a "principal" wavelength ( ⁇ 0 ), a "reference" wavelength ( ⁇ - ⁇ ) and an auxiliary wavelength ⁇ 2 .
• ⁇ 0 is selected to achieve high analyte absorption
• ⁇ 1 is selected to have minimal analyte absorption.
• ⁇ 1 is adjusted to have the same absorption in blood-less tissue as ⁇ 0 .
• the auxiliary wavelength ⁇ 2 is selected to have high absorption in a component of the fluid, and is used to provide an estimate of the fluid content of the sample matrix.
• the fiberless transflectance probe is used to measure the concentration of glucose (i.e. the target analyte) in blood (i.e. the fluid).
• ⁇ 0 is selected to be about 1620 nm and ⁇ 1 is selected to be about 1380 nm, which are in the near infrared energy spectrum.
• the auxiliary wavelength ⁇ 2 is selected to be about 525 nm, which is an isosbestic wavelength for hemoglobin, and provides an excellent sensitivity to blood.
• the three wavelengths, ⁇ 0 , ⁇ 1 , and ⁇ 2 are 1620 +/- 20 nm, 1380 +/- 20 nm, and 525 +/- 20 nm, respectively.
• the beam of electromagnetic radiation consists of time multiplexed component of the three different wavelengths ( ⁇ 0 , ⁇ 1 and ⁇ 2 ) alternating at a frequency of 100 Hz. In another embodiment, some or all wavelengths are on at ail times, i.e., they are not alternating. In certain embodiments, the separation of the signal into its wavelength components is performed by the detector or processor.
• FIG. 1 shows a conceptual diagram of an analyte testing device 10 which utilizes the Optical BridgeTM technology for noninvasively measuring the concentration of a target analyte (e.g. glucose) in a fluid (e.g. blood) within a sample matrix (e.g. a tissue matrix).
• the analyte testing device 10 comprises at least two laser diodes 12 and 14 operating at wavelengths ⁇ 0 and ⁇ 1 respectively, a signal detector 18, and an optical transflectance probe 20 which interfaces the laser diodes with a measurement site 22.
• the analyte testing device 10 further comprises at least one LED 16 operating at a wavelength ⁇ 2 .
• the beam through the optical probe 20 alternates between ⁇ 0 , ⁇ 1 and ⁇ 2 at a preselected frequency.
• the wavelength alternation is driven by the laser controller module 24.
• the measurement site 22 is chosen such that it is: 1) easily accessible, 2) well perfused with the fluid containing the target analyte; 3) small enough to fit in a sample port of a portable instrument, 4) can be easily compressed/ uncompressed.
• a subject's earlobe is used as the measurement site 22.
• the subject's finger is used as the measurement site 22.
• the extracellular-to-intracellular fluid ratio of the measurement site 22 is changed during the measurement by exerting varying mechanical pressure on the measurement site.
• the amount of fluid in the measurement site 22 is modulated by means of a linear actuator 26, as illustrated in FIG. 1.
• the linear actuator compresses the measurement site 22 with a pressure sufficient to displace fluid (with the target analyte) from the measurement site 22.
• the linear actuator compresses the measurement site 22 with a pressure three times systolic blood pressure. As the compressive force is released, the displaced fluid returns to the measurement site.
• linear actuator 26 compresses measurement site 22 against optical probe 20. In another embodiment, linear actuator 26 compresses optical probe 20 against measurement site 22.
• the Optical BridgeTM technology exploits the principle that compressed tissue has a relatively lower proportion of fluid with the target analyte than uncompressed tissue, although some residual amount of analyte remains in the measurement site 22 during the compression.
• the extracellular-to-intracellular fluid ratio is allowed to change as a result of natural pulsation due to heartbeat, and the measurement cycle is synchronized with such pulsation.
• the optical path of the radiation beam contains minimal fluid and the target analyte.
• the Optical BridgeTM balancing is performed at this position at the beginning of each measurement to achieve the maximum background rejection.
• the balancing is performed by adjusting the light intensities at the two wavelengths ⁇ 0 , ⁇ 1 , and also by modifying the reference wavelength ⁇ 1 .
• the variations in the background matrix structure are compensated for in the balancing process.
• the light intensities and the wavelength ⁇ 1 are adjusted such that the baseline absorption (indicated by the Optical Bridge Signal 28) is essentially zero when there is minimal fluid and analyte in the optical path, and the differential absorption of the wavelengths ⁇ 0 and ⁇ 1 (indicated by the variation in Detector Output Voltage 30) is minimum.
• the Optical Bridge Signal 28 is in effect the rectified Detector Output Voltage 30.
• the pressure on the measurement site 22 is relaxed after the Optical Bridge is balanced, allowing fluid to return to the site.
• the attenuation of the two wavelengths ⁇ 0 and ⁇ 1 is different at the uncompressed position, as indicated by the larger variation in the Detector Output Voltage 30 in FIG. 2B.
• the Optical Bridge Signal 28 is higher (i.e. there is more background absorption in the measurement site 22), as indicated in FIG. 2B.
• Variations in the Detector Output Voltage 30 is proportional to the changes in the amount of target analyte (e.g. glucose) in the fluid.
• target analyte e.g. glucose
• the variations of the amount of fluid in the measurement site must also be measured.
• the wavelength ⁇ 2 which is highly absorbed by a component of the fluid, and follows the same optical path as wavelengths ⁇ 0 and ⁇ 1 , is used to compensate for the changes in fluid volume in the measurement site.
• Features extracted from the detected ⁇ 2 signal are processed to produce an estimate of the fluid volume, which is then combined with the detected ⁇ 0 and ⁇ 1 signal output to produce an estimate of the concentration of analyte in the blood.
• an auxiliary radiation source 34 is used to detect pulse and to synchronize the measurement with the inrush of blood into the measurement site 22.
• the auxiliary radiation source 34 is a LED operating at 525 nm (an isosbestic wavelength for hemoglobin).
• the auxiliary radiation source 34 is directed at a portion of the sample matrix that maintains good circulation at all times.
• the radiation source 34 may be directed at a portion of the sample matrix, outside the measurement site 22, which is not compressed by the linear actuator 26.
• the radiation source 34 generates a pulse detection beam which is scattered by the tissue, and a fraction of the original beam is detected by the signal detector 18.
• the auxiliary radiation source 34 is operated prior to the measurement step to synchronize the start of the measurement process with a variation of the blood pressure.
• optical probe 20 is configured for transflectance measurements, wherein the radiation beam is inserted into the measurement site 22 and the backscattered beam is detected by the signal detector 18. The detector then generates a signal indicative of the differential absorption of the target analyte.
• An important consideration for such an embodiment is that the light reflected from the surface of the measurement site 22 should not reach the detector as it would overwhelm the backscattered light.
• transflectance measurement is performed using a bifurcated bundle of optical fibers, a first portion of which is adapted to receive light from the laser diodes operating at wavelengths ⁇ 0 and ⁇ 1 , and a second portion of which is adapted to conduct the backscattered light to the signal detector.
• the fiber bundle passes through the optical probe 20, and the common end of the fiber bundle is pressed against the measurement site 22 for the transflectance measurements.
• transflectance measurement is performed using a fiberless transflectance probe 20, as illustrated in FIG. 3A.
• the transflectance probe 20 interfaces laser diodes 12, 14, at least one LED 16 and the sample detector 18 with the measurement site 22.
• Transflectance probe 20 comprises a cylindrical optical rod 40 having a polished outer surface 45.
• the optical rod 40 is made of fused quartz and the outer surface 45 is coated with aluminum to increase the reflectivity of the surface.
• the optical rod 40 is a glass rod with aluminum coating on the outer surface 45.
• Optical rod 40 is positioned perpendicular to a round detection window 46.
• optical rod 40 The distal end 42 of optical rod 40 is inserted into a circular opening 44 in the detection window 46, such that the distalmost end of the optical rod is axially aligned with the distal surface 49 of the detection window, and is in direct contact with the surface of the measurement site 22.
• the optical rod 40 is coated with aluminum throughout its length, including the distal end 42 which is inserted into the detection window 46. Additionally, the optical rod 40 and the detection window 46 are tightly coupled to ensure that a substantial portion of the radiation backscattered from the measurement site 22 enters the optical rod 40.
• the electromagnetic radiation beam is transmitted to the measurement site 22 through the detection window 46 during a measurement.
• the detection window 46 acts as an interface between the sample matrix and device hardware.
• the detection window 46 is also used to apply mechanical pressure on the measurement site 22 during a compression/decompression procedure, as described earlier.
• the detection window 46 is comprised of glass or quartz.
• the detection window 46 is comprised of a thermoplastic polymer that has high transmittance in the wavelength range consisting of ⁇ 0 , ⁇ 1 , and ⁇ 2 , has low moisture absorbility and is suitable for injection molding.
• thermoplastic polymers include, but is not limited to, cyclic polyolefins (COP), polymethylmethacrylate (PMMA), and polystyrene (PS).
• the optical rod 40 is further surrounded by a tapered tubular housing 50 having an inner reflective surface.
• the inner surface 52 is aluminized to increase the reflectivity of the surface.
• the distal end 54 of the tapered tubular housing 50 is coupled with the detection window 46, as shown in FIG. 3B.
• the tapered tubular housing 50 is made of quartz or glass.
• the tapered tubular housing 50 is made of a thermoplastic polymer using injection molding, and the inner surface 52 is coated with aluminum to increase the reflectivity of the surface.
• the detection window 46 and the tapered tubular housing 50 are injected molded together using the same thermoplastic polymer.
• the tapered tubular housing 50 also facilitates shaping of the radiation beam emitted by the laser diodes and the LEDs.
• the shape of the inner surface 52 and taper angle of the tubular housing guides the distribution of the emitted beam on the measurement site 22.
• the tubular housing 50 is configured as a truncated conical shell having a cone angle (angle between the longitudinal angle and wall) of 7.5°.
• the inner surface of tapered tubular housing 50 is faceted in order to distribute the incident light evenly on the measurement site 22.
• the number of facets in the tubular housing corresponds to the number of laser diodes and LEDs used in the optical probe 20.
• the optical probe 20 includes four laser diodes (two each for the wavelengths ⁇ 0 and ⁇ 1 ), and two LEDs operating at wavelength ⁇ 2 .
• the inner surface 52 of the tapered tubular housing 50 has a faceted hexagonal shape, as shown in FIGS. 3A and 3B.
• the facets on the inner surface 52 are in the form of a convex cylinder, and the radius of curvature of each facet is optimized for the corresponding light source to provide an uniform distribution of light from the different sources on the measurement site 22.
• the fiberless transflectance probe 20 is used in a optical detection system to measure the concentration of glucose in blood.
• ⁇ 0 is selected to be 1620 nm and ⁇ 1 is selected to be 1380 nm, and the radii of curvature of the cylindrical facets associated with the lasers operating at ⁇ 0 and ⁇ 1 are 7.2 mm and 6.1 mm, respectively.
• the distance of the laser diodes 12, 14 from the central longitudinal axis of the tubular housing guides the distribution of the emitted beam on the measurement site 22.
• the distance of the laser diodes from the central axis is 5.3 mm.
• the laser diodes 12, 14 are mounted on a heat sink 60 at the proximal end 56 of tapered tubular housing 50 for temperature stability.
• the LEDs 16 are also mounted on the heat sink adjacent to the laser diodes.
• the LEDs are mounted on a positioning plate 62 below the heat sink 60, as shown in FIG. 3A, to maintain a stabilized operating condition for the laser diodes.
• the radiation beam comprising the wavelengths ⁇ 0 , ⁇ 1 , and ⁇ 2 , is transmitted to the measurement site 22 by reflecting on the outer surface 45 of the optical rod 40 and the inner surface 52 of the tapered tubular housing 50.
• FIG. 4 shows the distribution of light from four laser diodes on the measurement site 22. As shown in the figure, the light from the multiple sources is distributed angularly uniformly on the measurement site, with the area surrounding the optical rod 40 receiving more radiation than the area around the edge of the tubular housing 50. Some of the light incident on the measurement site 22 is backscattered by the sample, and a fraction of the backscattered light reaches the interior of the optical rod 40 and is conducted to the signal detector 18 by reflecting on the inner surface of the optical rod.
• the sample detector 18 (not shown in FIG. 3A) is positioned at the proximal end 44 of the optical rod 40.
• an alternating signal is generated which is proportional to the differential absorption of wavelengths ⁇ 0 and ⁇ 1 by the fluid in the sample matrix.
• the concentration of the target analyte in the fluid is then calculated from the output signal using a signal processing algorithm.
• the analyte testing device 10 is a handheld unit.
• the handheld unit comprises a screen 27 for graphic display of the measurement results
• the on-board electronics consist of a processor 23 for operating the device and calculating the target analyte concentration, and a control module 24 for driving the laser diodes 12, 14 and LEDs 16.
• the handheld unit may be powered from an external power supply, rechargeable batteries, or through an USB port.
• the handheld analyte testing device 10 consists of a memory 25 which stores the measurement results.
• the memory 25 may further contain interactive instructions for using and operating the device to be displayed on the screen 27.
• the instructions may comprise an interactive feature-rich presentation including a multimedia recording providing audio/video instructions for operating the device, or alternatively simple text, displayed on the screen, illustrating step-by-step instructions for operating and using the device.
• the inclusion of interactive instructions with the device eliminates the need for extensive training for use, allowing for patient self-testing and use by persons other than medical professionals.
• the memory 25 may also contain a reference database for statistical calibration of the device.
• the reference database may be accessed from a remote storage device via a wireless or a wired connection. Similarly, data collected from the subject by the analyte testing device 10 may be recorded in the database for future reference.
• the analyte testing device 10 can be a standalone system or can operate in conjunction with a mobile or stationary device to facilitate display or storage of data, and to signal healthcare personnel when therapeutic action is needed, if the device is used for continuous monitoring of a diagnostic parameter associated with a disease state.
• Mobile devices can include, but are not limited to, handheld devices and wireless devices distant from, and in communication with, the analyte testing device 10.
• Stationary devices can include, but are not limited to, desktop computers, printers and other peripherals that display or store the results of the test.
• the analyte testing device 10 stores each patient file, which includes a summary of the session and test results, on a removable memory card 21 , such as compact flash (CF) card.
• CF compact flash
• results from the processor 23 are transferred directly to an external mobile or stationary device to facilitate display or storage of data.
• the results from the processor 23 may be displayed or stored on a PC 29 using a PC interface, such as an USB port, IRDA port, BLUETOOTH® or other wireless link.
• the results can be transmitted wirelessly or via a cable to a printer 31 that prints the results to be used by attending medical personnel.
• the analyte testing device 10 can transmit data to another mobile or stationary device to facilitate more complex data processing or analysis.
• the device, operating in conjunction with PC 29, can send data to be further processed by the computer.
• the Optical BridgeTM method and the analyte testing device 10 are described here with a focus towards measuring the concentration of glucose in blood, the method and device presented in this disclosure may also be employed to detect the concentration of other analytes, such as urea, cholesterol, nicotine, drugs, etc., in blood or other fluids. Additionally, the fiberless transflectance probe 20 and its method of use may be utilized in any optical detection system operating in the infrared, visible, or ultraviolet wavelength range.

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• 2012
  • 2012-04-06 US US13/441,467 patent/US20130267799A1/en not_active Abandoned
• 2013
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  • 2013-04-04 WO PCT/US2013/035250 patent/WO2013152177A1/en active Application Filing
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